Connect public, paid and private patent data with Google Patents Public Datasets

Arrangements for coherence topographic ray tracing on the eye

Download PDF

Info

Publication number
US6788421B2
US6788421B2 US10167130 US16713002A US6788421B2 US 6788421 B2 US6788421 B2 US 6788421B2 US 10167130 US10167130 US 10167130 US 16713002 A US16713002 A US 16713002A US 6788421 B2 US6788421 B2 US 6788421B2
Authority
US
Grant status
Grant
Patent type
Prior art keywords
beam
eye
reference
light
measurement
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired - Fee Related
Application number
US10167130
Other versions
US20030053072A1 (en )
Inventor
Adolf Friedrich Fercher
Roland Barth
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Jenoptik AG
Original Assignee
Jenoptik AG
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Grant date

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/113Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for determining or recording eye movement
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/107Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for determining the shape or measuring the curvature of the cornea
    • GPHYSICS
    • G01MEASURING; TESTING
    • G01BMEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00Instruments as specified in the subgroups and characterised by the use of optical measuring means
    • G01B9/02Interferometers for determining dimensional properties of, or relations between, measurement objects
    • G01B9/02015Interferometers for determining dimensional properties of, or relations between, measurement objects characterised by a particular beam path configuration
    • G01B9/02029Combination with non-interferometric systems, i.e. for measuring the object
    • GPHYSICS
    • G01MEASURING; TESTING
    • G01BMEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00Instruments as specified in the subgroups and characterised by the use of optical measuring means
    • G01B9/02Interferometers for determining dimensional properties of, or relations between, measurement objects
    • G01B9/02055Interferometers for determining dimensional properties of, or relations between, measurement objects characterised by error reduction techniques
    • G01B9/02075Interferometers for determining dimensional properties of, or relations between, measurement objects characterised by error reduction techniques of particular errors
    • G01B9/02076Caused by motion
    • G01B9/02077Caused by motion of the object
    • GPHYSICS
    • G01MEASURING; TESTING
    • G01BMEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B9/00Instruments as specified in the subgroups and characterised by the use of optical measuring means
    • G01B9/02Interferometers for determining dimensional properties of, or relations between, measurement objects
    • G01B9/02091Tomographic low coherence interferometers, e.g. optical coherence tomography

Abstract

Topographic measurement of eye structures based on short coherence interferometry is the subject of the invention. The problem occurring in this connection is that longitudinal and transverse eye movements during signal registration lead to errors in the measured structure. The influences of longitudinal eye movements are compensated in that the reference beam, independent from the measurement beam, is directed to the corneal vertex and is reflected at the latter. The influences of longitudinal eye movements are minimized in that the transverse position of the eye is monitored by means of a direction-dependent registration of the light reflected at the corneal vertex by means of a diode array or a four-quadrant diode and transverse misalignment is detected and compensated.

Description

CROSS-REFERENCE TO RELATED APPLICATIONS

This application claims German Application No. 101 28 219.2, filed Jun. 11, 2001, the complete disclosure of which is hereby incorporated by reference.

BACKGROUND OF THE INVENTION

a) Field of the Invention

The invention is directed to topographic measurement of eye structures such as the cornea and lens in ophthalmology.

b) Description of the Related Art

As the result of new developments in ophthalmology which are characterized by many different types of surgical procedures on the lens of the eye (e.g., cataract surgery) and on the cornea (refractive cornea surgery), there is a considerable demand for measurement methods which quantify the entire structure of the eye topographically. While several methods known under the heading of ray tracing can determine the modulation transfer function and accordingly also the point spread function of the eye [for example, R. Navarro, E. Moreno, C. Dorronsoro, J. Opt. Soc. Am., Vol. 15 (1998): 2521-2529], these methods only measure the total effect of all optical components of the eye and do not provide any information about the influences of the individual components of the eye and particularly about the exact geometry of these components. However, in order to analyze what ophthalmologic procedure has what effect on the eye or, conversely, what influence is exerted by what optic component of the eye, it is necessary to know the exact geometry of all optically active components. For this purpose, the topography of the intraocular boundary surfaces must be measured.

Coherence topograms, described in A. F. Fercher and C. K. Hitzenberger in Springer Series in Optical Sciences (ed. T. Asakura), Vol. 4, Springer Verlag, Berlin 1999, are a suitable optical method for this purpose. Optical coherence topograms are obtained from a series of z-signals measured in longitudinal direction by short coherence interferometry from object areas which are adjacent in transverse x-direction by scanning the optical length of the reference arm of a two-beam interferometer. In the method described in the literature cited above, the measurement beam and reference beam always extend coaxially and centrally through the pupil of the eye. Therefore, it can only be used to acquire the geometry of the fundus, but not for partial length topography of the entire eye. Further, measurement errors are caused by transverse misalignments transverse to the axis of the eye during signal registration.

Another optical method which is suitable for this purpose is described in J. A. Izatt, M. R. Hee, D. Huang, J. G. Fujimoto, E. A. Swanson, C. P. Lin, J. S. Schuman, C. A Puliafito, SPIE Proc., 1877 (1993): 136-144. This relates to the method of optical coherence tomography (OCT). However, this method fundamentally suffers from the problem that eye movements during signal registration lead to errors in the measured structure. In particular, longitudinal movements in direction of the axis of the eye cause a falsification of the depth position or z-position of the measured structures.

OBJECT AND SUMMARY OF THE INVENTION

Therefore, it is the primary object of the invention to provide arrangements for coherence topography of the eye by means of a series of depth signals which are measured by means of short coherence interferometry in different pupil points by scanning the optical length of the reference arm of a two-beam interferometer, wherein longitudinal movements in direction of the axis of the eye and transverse movements transverse to the axis of the eye do not cause a falsifying of the positions of the measured structures, and longitudinal depth signals or z-signals can be obtained at selected points in the pupil of the eye also outside of the visual axis.

This object is met in that the measurement beam of a short coherence interferometer is radiated into the pupil of the eye in a series of measurement positions and the reference beam, independent from the measurement beam, is fixedly directed to the corneal vertex and reflected at the latter. Every longitudinal movement of the eye then leads to the same phase displacement in the reference beam as in the measurement beam and has no effect on the short coherence interferometry. Further, the transverse position of the eye is monitored by means of a direction-dependent registration of the light reflected at the corneal vertex by means of a diode array or a four-quadrant diode and a criterion is obtained for the transverse alignment of the eye with respect to the beam axis. Transverse misalignments can be detected and compensated in this way. Finally, a pair of deflecting mirrors whose axes of rotation are oriented normal to one another is used for controlling the measurement beam at selected pupil points.

In the following, the invention will be described with reference to the figures.

BRIEF DESCRIPTION OF THE DRAWINGS

In the drawings:

FIG. 1 describes the basic method according to the invention;

FIG. 2 shows an equidistant arrangement of measurement points on the eye;

FIG. 3 describes how the measurement beam can be controlled at different points on the pupil of the eye; and

FIG. 4 describes an alternative in which the scanning of the optical length of the reference beam is replaced by the scanning of the optical length of the object beam.

DESCRIPTION OF THE PREFERRED EMBODIMENTS

FIG. 1 shows the beam path of the topographic short coherence interferometer. The light beam 1 of a partial temporal coherent light source 2, for example, a superluminescent diode, illuminates the interferometer. This light beam is divided into measurement beam 4 and reference beam 5 at the beam splitter 3. The measurement beam 4 is deflected by the rotating or oscillating (double-arrow 30) deflecting mirror 6 to the partially reflecting plate 7 and then through the objective 8 to the eye 9. The deflecting mirror 6 is located in the focal plane of the optics 8. In the eye, this light beam is directed through various tissue such as the cornea 10 and lens 11 through the aqueous humour 12 and the vitreous body 13 to the ocular fundus 14. Light which is backscattered in the direction of the incident measurement beam 4 by this tissue and its boundary surfaces and by the ocular fundus takes, as light beam 15, the same path as the measurement beam 4 up until the beam splitter 3, but in the opposite direction. The returning light beam 15 penetrates the beam splitter 3 and strikes the photodetector 16. The longitudinal depth positions of the light-reemitting locations are determined from the photoelectric signal U of the photodetector 16 by known methods of short coherence interferometry.

When a short coherent light source emitting short-wave light (e.g., blue-radiating laser diode) is used in the two-beam interferometer instead of the conventional superluminescent diode mentioned above, the light components (that is, light beam 15) which are reemitted by the intraocular tissues, i.e., the cornea 10, lens 11, vitreous body 13 and ocular fundus 14, are appreciably more pronounced. Since the signals obtained at the photodetector 16 have a greater amplitude, a more precise interferometric depth determination of the light-reemitting layers is possible.

The reference beam 5 passes through the beam splitter 20, is reflected by the reference mirror 21 and is then directed from beam splitter 20 through beam splitters 42 and 22 and the partially reflecting plate 7 and is focused on the corneal vertex 23 by the objective 8. The light bundle 24 reflected at the corneal vertex 23 travels back along the same path as the reference beam 5 and is reflected by the beam splitter 3 onto the photodetector 16. Further, a portion of this light bundle passes through the beam splitter 20 in a straight line and then through a lens 75 to allow the observer 31 to visually monitor the centering of the eye with respect to the axis of the reference beam 5.

In short coherence interferometry, the optical path length of the reference beam 5 is scanned; that is, during the “z-scan”, as it is called, the reference mirror 21 is moved along the axis of the reference beam 5 in the direction indicated by the double-arrow 32. When the path length of the reference beam 5 from the beam splitter 3 to the corneal vertex 23 and back within the coherence length Ic of the light beam 1 is equal to the path length of the measurement beam 4 from the beam splitter 3 to a light-reemitting location in the eye 9 and back to the beam splitter 3, interference occurs at the photodetector 16. By continuously displacing the reference mirror 21, the z-position of light-reemitting locations in the object is registered by means of the interference occurring at the photodetector 16. The z-position is determined with an accuracy given approximately by the coherence length I c λ 2 Δ λ

of the utilized light, where λ is the average wavelength and Δλ is the wavelength bandwidth of the utilized radiation. In order to acquire the x-coordinate, either the object is moved in x-direction or, as is indicated in FIG. 1, the measurement beam scans the x-coordinates at the object 1 by means of a rotating or oscillating rotating mirror 6. The measurement beam 4 is accordingly moved normal to the visual axis 27 of the eye (double-arrow 33).

The light bundle 24 returning from the corneal vertex is reflected by the beam splitter 22 to the optics 25. The optics 25, together with optics 8, project an image of the light spot generated on the corneal vertex 23 by the reference beam 5 onto a diode array, for example, a four-quadrant diode 26. In this way, a direction-sensitive registration of the light bundle reflected at the cornea is obtained.

When the reference beam 5 is located on the visual axis 27 of the eye, a rotation-symmetric light spot occurs on the diode array. When the reference beam 5 is located outside of the optic axis 27 of the eye, it is reflected more laterally in a corresponding manner and the brightness distribution in the light spot on the photodetector array 26 deviates from the rotational symmetry of the eye. The centering of the eye with reference to the axis of the reference beam 5 can be assessed based on the value of the signal of the diode array. These signals can then be used for readjusting the centering, for example, by displacing the interferometer relative to the eye and/or the registration of the z-signals measured by short coherence interferometry can be interrupted when a threshold value is exceeded. In this way, measurement errors due to transverse misalignment of the eye can be drastically reduced. It is noted that instead of the reference beam 5 another light beam which is reflected in coaxial to the reference beam could also be reflected in for readjustment of centering. A light beam of this kind can be generated by a lamp 40, collimated through optics 41 and reflected in coaxial to the axis of the reference beam 5 by means of a beam splitter 42.

Longitudinal movements in direction of the axis of the eye which lead to falsified z-positions of the measured structures are compensated by the arrangement according to the invention because the reference beam 5 is reflected at the corneal vertex. In this case, every longitudinal movement of the eye leads to the same phase displacement in the reference beam as in the measurement beam. This also simplifies the interpretation of the measured object structure: all z-signals measured by short coherence interferometry have their reference point in a plane 34 tangential to the corneal vertex 23.

The topographic data acquisition at the eye can be carried out in two dimensions or in three dimensions. In two-dimensional data acquisition, the measurement positions can be equidistant along a straight line, for example, along a pupil diameter, as is indicated in FIG. 2 by the points 61 lying on the straight line 60. The edge of the pupil is indicated by 62. This results in topograms corresponding to FIG. 1 in A. F. Fercher and C. K. Hitzenberger, Springer Series in Optical Sciences (ed. T. Asakura), Vol. 4, Springer Verlag, Berlin 1999. For three-dimensional data acquisition, the measurement positions in the entire pupil surface (x- and y-coordinates) can be distributed in an equidistant manner, for example, or can be distributed over the pupil in a comb-shaped or wavy manner. The three-dimensional coordinates of the cornea surfaces and lens surfaces are then obtained together with the z-coordinates of short coherence interferometry. In order to implement topographic data acquisition in this manner, it must be possible to control the measurement beam at selected locations on the (two-dimensional) pupil. As is described in FIG. 3, this is possible by means of a pair of scanning mirrors 72 and 72′ whose axes of rotation extend normal to one another. In FIG. 3, for example, the axis of rotation of mirror 72 lies in the drawing plane and the axis of rotation of mirror 72′ is oriented normal to the drawing plane.

Finally, it is noted that the scanning of the reference beam can also be carried out in another way other than by the moving mirror 21, for example, by arrangements such as those described in Application A 472/99, “Periodically operating optical path length modulator”. The scanning of the optical length of the reference arm can also be replaced by scanning the optical length of the measurement arm, as is shown in FIG. 4. In this case, the measurement beam 4 is reflected to a roof prism 51 by a deflecting mirror 50 and is reflected back from the roof prism 51 via the deflecting mirror 52 to the deflecting mirror 6. In this case, the scanning of the optical length of the measurement arm is carried out by moving the roof prism 51 in the direction indicated by the double-arrow 53.

Another advantageous embodiment form of the invention consists in the use of a short coherent light source 2 emitting short-wave light in the two-beam interferometer (e.g., blue-radiating laser diode). Accordingly, the light components (that is, light beam 15) which are reemitted by the intraocular tissues, i.e., the cornea 10, lens 11, vitreous body 13 and ocular fundus 14, are appreciably more pronounced than in conventional short coherence interferometers which use light sources in the near infrared range according to the prior art. Since the signals obtained in this way have a greater amplitude, a more precise detection and, therefore, more precise interferometric depth determination of the light-reemitting layers is possible.

While the foregoing description and drawings represent the present invention, it will be obvious to those skilled in the art that various changes may be made therein without departing from the true spirit and scope of the present invention.

Reference Numbers

 1 partially coherent light beam
 2 short coherence light source
 3 beam splitter
 4 measurement beam
 5 reference beam
 6 rotating or oscillating deflecting mirror
 7 partially reflecting plate
 8 objective
 9 eye
10 cornea
11 eye lens
12 aqueous humour
13 vitreous body
14 ocular fundus
15 reemitted measurement beam
16 photodetector
20 beam splitter
21 reference mirror
22 beam splitter
23 corneal vertex
24 reflected reference beam
25 optics
26 detector array, four-quadrant diode
27 visual axis of the eye
30 movement direction of the rotating or oscillating deflecting
mirror
31 observer
32 movement direction of the reference mirror
33 movement direction of the measurement beam
34 plane tangent to the corneal vertex
40 light source
41 optics
42 beam splitter
50 deflecting mirror
51 roof prism
52 deflecting mirror
53 movement direction of the roof prism
70 deflecting mirror
71 roof prism
72 and 72′ pair of rotating mirrors
73 axis of rotation of the rotating mirror 72
74 and 74′ rotating movements of the pair of rotating mirrors 72 and 72′

Claims (5)

What is claimed is:
1. An arrangement for coherence topography of the eye by a series of depth signals which are measured by short coherence interferometry in different pupil points by scanning an optical length of a reference arm of a two-beam interferometer, comprising that:
a first device that radiates a measurement beam of a short coherence interferometer into the pupil of an eye in a series of measurement positions; and
a second device that fixedly directs a reference beam, independent from the measurement beam, to the corneal vertex, the reference beam being reflected at the corneal vertex.
2. The arrangement according to claim 1, further comprising a diode array or four-quadrant diode that monitors the position of the eye transverse to a depth position of the eye by a direction-dependent registration of the light reflected at the corneal vertex and a criterion is obtained for the transverse alignment of the eye with respect to the beam axis.
3. The arrangement according to claim 1, wherein the short coherent interferometer radiates short-wave light.
4. An arrangement for coherence topography of an eye by a series of depth signals that are measured by short coherence interferometry in different pupil points by scanning an optical length of a reference arm of a two-beam interferometer, comprising:
a first light source that provides a short wave measurement beam below an NIR range;
a second light source that provides a reference beam;
a first device that guides the measurement beam into the pupil of the eye at a series of measurement positions; and
a second device that fixedly directs the reference beam, independent from the measurement beam, to the corneal vertex which is reflected at the corneal vertex; and
a detector that receives both the reflected reference beam and the measurement beam returning from the eye.
5. The arrangement according to claim 4, wherein a single source generates both the reference beam and the measurement beam.
US10167130 2001-06-11 2002-06-10 Arrangements for coherence topographic ray tracing on the eye Expired - Fee Related US6788421B2 (en)

Priority Applications (3)

Application Number Priority Date Filing Date Title
DE2001128219 DE10128219A1 (en) 2001-06-11 2001-06-11 Topographic measurement of the eye structure, such as the cornea and eye lens by use of coherence-topography with depth measurements insensitive to longitudinal and transverse movements of the reference arm of the instrument
DE10128219 2001-06-11
DE10128219.2 2001-06-11

Publications (2)

Publication Number Publication Date
US20030053072A1 true US20030053072A1 (en) 2003-03-20
US6788421B2 true US6788421B2 (en) 2004-09-07

Family

ID=7687870

Family Applications (1)

Application Number Title Priority Date Filing Date
US10167130 Expired - Fee Related US6788421B2 (en) 2001-06-11 2002-06-10 Arrangements for coherence topographic ray tracing on the eye

Country Status (3)

Country Link
US (1) US6788421B2 (en)
JP (1) JP4021242B2 (en)
DE (1) DE10128219A1 (en)

Cited By (11)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20060066869A1 (en) * 2004-09-30 2006-03-30 Nidek Co., Ltd. Optical coherence tomography apparatus based on spectral interference and an ophthalmic apparatus
US20060187462A1 (en) * 2005-01-21 2006-08-24 Vivek Srinivasan Methods and apparatus for optical coherence tomography scanning
US20080198366A1 (en) * 2007-02-21 2008-08-21 Leblanc Philip Robert Apparatus for measuring defects in a glass sheet
US20090168017A1 (en) * 2007-12-26 2009-07-02 O'hara Keith E Refractive prescription using optical coherence tomography
US7784942B2 (en) 2006-10-04 2010-08-31 Kabushiki Kaisha Topcon Fundus oculi observation device, a fundus oculi image display device and a fundus oculi image display method
US20100245838A1 (en) * 2005-01-21 2010-09-30 Carl Zeiss Meditec, Inc. Method of motion correction in optical coherence tomography imaging
DE102009022958A1 (en) 2009-05-28 2010-12-02 Carl Zeiss Meditec Ag Apparatus and method for optical measurement of relative distances
US8649611B2 (en) 2005-04-06 2014-02-11 Carl Zeiss Meditec, Inc. Method and apparatus for measuring motion of a subject using a series of partial images from an imaging system
US8857988B2 (en) 2011-07-07 2014-10-14 Carl Zeiss Meditec, Inc. Data acquisition methods for reduced motion artifacts and applications in OCT angiography
US9033510B2 (en) 2011-03-30 2015-05-19 Carl Zeiss Meditec, Inc. Systems and methods for efficiently obtaining measurements of the human eye using tracking
US9101294B2 (en) 2012-01-19 2015-08-11 Carl Zeiss Meditec, Inc. Systems and methods for enhanced accuracy in OCT imaging of the cornea

Families Citing this family (47)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US6847449B2 (en) * 2002-11-27 2005-01-25 The United States Of America As Represented By The Secretary Of The Navy Method and apparatus for reducing speckle in optical coherence tomography images
DE102004037479A1 (en) * 2004-08-03 2006-03-16 Carl Zeiss Meditec Ag Fourier-domain OCT ray tracing on the eye
JP4916779B2 (en) * 2005-09-29 2012-04-18 株式会社トプコン Fundus observation device
JP4850495B2 (en) 2005-10-12 2012-01-11 国立大学法人 筑波大学 A fundus observation device and fundus observation program
JP4819478B2 (en) * 2005-10-31 2011-11-24 株式会社ニデック Ophthalmic imaging apparatus
EP1806092A1 (en) 2006-01-10 2007-07-11 Kabushiki Kaisha TOPCON A fundus observation device
JP2007181631A (en) * 2006-01-10 2007-07-19 Topcon Corp Fundus observation system
JP4884777B2 (en) 2006-01-11 2012-02-29 株式会社トプコン Fundus observation device
JP4823693B2 (en) 2006-01-11 2011-11-24 株式会社トプコン The optical image measurement device
JP4890878B2 (en) 2006-02-16 2012-03-07 株式会社トプコン Fundus observation device
JP4869756B2 (en) * 2006-03-24 2012-02-08 株式会社トプコン Fundus observation device
JP4869757B2 (en) 2006-03-24 2012-02-08 株式会社トプコン Fundus observation device
JP4864516B2 (en) 2006-04-07 2012-02-01 株式会社トプコン Ophthalmic apparatus
JP4864515B2 (en) 2006-04-07 2012-02-01 株式会社トプコン Fundus observation device
JP4855150B2 (en) 2006-06-09 2012-01-18 株式会社トプコン Fundus observation device, an ophthalmologic image processing apparatus and an ophthalmologic image processing program
JP2008035944A (en) 2006-08-02 2008-02-21 Topcon Corp System for ophthalmologic imaging
JP5007114B2 (en) 2006-12-22 2012-08-22 株式会社トプコン Fundus observation device, the fundus image display device and program
JP4996917B2 (en) 2006-12-26 2012-08-08 株式会社トプコン Program for controlling the optical image measuring apparatus and an optical image measurement device
JP4996918B2 (en) 2006-12-26 2012-08-08 株式会社トプコン Program for controlling the optical image measuring apparatus and an optical image measurement device
EP1950526B1 (en) 2007-01-26 2010-03-10 Kabushiki Kaisha TOPCON Optical image measurement device
JP5017079B2 (en) 2007-01-26 2012-09-05 株式会社トプコン The optical image measurement device
JP4921201B2 (en) 2007-02-23 2012-04-25 株式会社トプコン Program for controlling the optical image measuring apparatus and an optical image measurement device
JP5058627B2 (en) 2007-02-26 2012-10-24 株式会社トプコン Fundus observation device
JP5061380B2 (en) 2007-03-23 2012-10-31 株式会社トプコン Fundus observation device, an ophthalmologic image display device and program
JP5523658B2 (en) 2007-03-23 2014-06-18 株式会社トプコン The optical image measurement device
JP4994911B2 (en) * 2007-03-28 2012-08-08 株式会社トプコン The optical image measurement device
JP4896794B2 (en) 2007-03-30 2012-03-14 株式会社トプコン Optical image measuring apparatus, a program, and an optical image measurement method to control it
JP4971864B2 (en) 2007-04-18 2012-07-11 株式会社トプコン Optical image measuring apparatus and a program for controlling the
JP4971863B2 (en) 2007-04-18 2012-07-11 株式会社トプコン The optical image measurement device
JP4971872B2 (en) 2007-05-23 2012-07-11 株式会社トプコン The fundus oculi observation device and a program for controlling the
JP5138977B2 (en) 2007-05-24 2013-02-06 株式会社トプコン The optical image measurement device
JP5032203B2 (en) 2007-05-24 2012-09-26 株式会社トプコン The fundus oculi observation device and a program for controlling the
US7641339B2 (en) 2007-07-31 2010-01-05 Kabushiki Kaisha Topcon Ophthalmologic information processing apparatus and ophthalmologic examination apparatus
JP5117787B2 (en) 2007-08-13 2013-01-16 株式会社トプコン The optical image measurement device
JP4940070B2 (en) 2007-09-10 2012-05-30 国立大学法人 東京大学 Fundus observation device, an ophthalmologic image processing apparatus and program
JP4466968B2 (en) * 2008-11-10 2010-05-26 キヤノン株式会社 The image processing apparatus, Ezo processing method, program, and program storage medium
JP4949504B2 (en) * 2010-06-18 2012-06-13 株式会社ニデック Ophthalmic imaging apparatus
US9055892B2 (en) * 2011-04-27 2015-06-16 Carl Zeiss Meditec, Inc. Systems and methods for improved ophthalmic imaging
CN102335088B (en) * 2011-07-15 2013-05-08 中国科学院光电技术研究所 Human eye laser interference fringe visual perception learning and training instrument
JP5367047B2 (en) * 2011-10-24 2013-12-11 株式会社トプコン Fundus observation device
JP5255711B2 (en) * 2012-01-30 2013-08-07 株式会社ニデック Ophthalmic imaging apparatus
JP6071304B2 (en) * 2012-07-30 2017-02-01 キヤノン株式会社 Ophthalmic apparatus and alignment method
JP5209143B2 (en) * 2012-10-23 2013-06-12 株式会社トプコン Fundus observation device
JP6057210B2 (en) 2012-12-13 2017-01-11 株式会社トプコン Optical property measurement apparatus and optical property measuring method
JP5319010B2 (en) * 2012-12-28 2013-10-16 株式会社ニデック Ophthalmic imaging apparatus
JP5319009B2 (en) * 2012-12-28 2013-10-16 株式会社ニデック Fundus image display device, and ophthalmologic imaging apparatus including the same.
JP5306554B2 (en) * 2013-03-18 2013-10-02 株式会社ニデック Ophthalmic imaging apparatus

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5459570A (en) * 1991-04-29 1995-10-17 Massachusetts Institute Of Technology Method and apparatus for performing optical measurements
US5719673A (en) * 1995-02-10 1998-02-17 Carl Zeiss Jena Gmbh Interferometer arrangement with adjustable optical path length difference for detecting a distance between different layers of an eye
US6307634B2 (en) * 1998-05-15 2001-10-23 Laser Diagnostic Technologies, Inc. Method and apparatus for recording three-dimensional distribution of light backscattering potential in transparent and semi-transparent structures

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5459570A (en) * 1991-04-29 1995-10-17 Massachusetts Institute Of Technology Method and apparatus for performing optical measurements
US5719673A (en) * 1995-02-10 1998-02-17 Carl Zeiss Jena Gmbh Interferometer arrangement with adjustable optical path length difference for detecting a distance between different layers of an eye
US6307634B2 (en) * 1998-05-15 2001-10-23 Laser Diagnostic Technologies, Inc. Method and apparatus for recording three-dimensional distribution of light backscattering potential in transparent and semi-transparent structures

Cited By (26)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20060066869A1 (en) * 2004-09-30 2006-03-30 Nidek Co., Ltd. Optical coherence tomography apparatus based on spectral interference and an ophthalmic apparatus
US7768651B2 (en) * 2004-09-30 2010-08-03 Nidek Co., Ltd. Optical coherence tomography apparatus based on spectral interference and an ophthalmic apparatus
US20060187462A1 (en) * 2005-01-21 2006-08-24 Vivek Srinivasan Methods and apparatus for optical coherence tomography scanning
US9167964B2 (en) 2005-01-21 2015-10-27 Carl Zeiss Meditec, Inc. Method of motion correction in optical coherence tomography imaging
US8711366B2 (en) 2005-01-21 2014-04-29 Carl Zeiss Meditec, Inc. Method of motion correction in optical coherence tomography imaging
US8405834B2 (en) 2005-01-21 2013-03-26 Massachusetts Institute Of Technology Methods and apparatus for optical coherence tomography scanning
US8115935B2 (en) * 2005-01-21 2012-02-14 Carl Zeiss Meditec, Inc. Method of motion correction in optical coherence tomography imaging
US20110134394A1 (en) * 2005-01-21 2011-06-09 Massachusetts Institute Of Technology Methods and apparatus for optical coherence tomography scanning
US20100245838A1 (en) * 2005-01-21 2010-09-30 Carl Zeiss Meditec, Inc. Method of motion correction in optical coherence tomography imaging
US7884945B2 (en) 2005-01-21 2011-02-08 Massachusetts Institute Of Technology Methods and apparatus for optical coherence tomography scanning
US9706915B2 (en) 2005-01-21 2017-07-18 Carl Zeiss Meditec, Inc. Method of motion correction in optical coherence tomography imaging
US9033504B2 (en) 2005-04-06 2015-05-19 Carl Zeiss Meditec, Inc. Method and apparatus for measuring motion of a subject using a series of partial images from an imaging system
US8649611B2 (en) 2005-04-06 2014-02-11 Carl Zeiss Meditec, Inc. Method and apparatus for measuring motion of a subject using a series of partial images from an imaging system
US7784942B2 (en) 2006-10-04 2010-08-31 Kabushiki Kaisha Topcon Fundus oculi observation device, a fundus oculi image display device and a fundus oculi image display method
US7808653B2 (en) 2007-02-21 2010-10-05 Corning Incorporated Apparatus for measuring defects in a glass sheet
US20090237654A1 (en) * 2007-02-21 2009-09-24 Leblanc Philip Robert Apparatus for measuring defects in a glass sheet
US7570366B2 (en) * 2007-02-21 2009-08-04 Corning Incorporated Apparatus for measuring defects in a glass sheet
US20080198366A1 (en) * 2007-02-21 2008-08-21 Leblanc Philip Robert Apparatus for measuring defects in a glass sheet
US7878651B2 (en) 2007-12-26 2011-02-01 Carl Zeiss Meditec, Inc. Refractive prescription using optical coherence tomography
US20090168017A1 (en) * 2007-12-26 2009-07-02 O'hara Keith E Refractive prescription using optical coherence tomography
US20100302550A1 (en) * 2009-05-28 2010-12-02 Carl Zeiss Meditec Ag Device and method for the optical measurement of relative distances
DE102009022958A1 (en) 2009-05-28 2010-12-02 Carl Zeiss Meditec Ag Apparatus and method for optical measurement of relative distances
US9033510B2 (en) 2011-03-30 2015-05-19 Carl Zeiss Meditec, Inc. Systems and methods for efficiently obtaining measurements of the human eye using tracking
US8857988B2 (en) 2011-07-07 2014-10-14 Carl Zeiss Meditec, Inc. Data acquisition methods for reduced motion artifacts and applications in OCT angiography
US9101294B2 (en) 2012-01-19 2015-08-11 Carl Zeiss Meditec, Inc. Systems and methods for enhanced accuracy in OCT imaging of the cornea
US9706914B2 (en) 2012-01-19 2017-07-18 Carl Zeiss Meditec, Inc. Systems and methods for enhanced accuracy in OCT imaging of the cornea

Also Published As

Publication number Publication date Type
JP2003000543A (en) 2003-01-07 application
JP4021242B2 (en) 2007-12-12 grant
US20030053072A1 (en) 2003-03-20 application
DE10128219A1 (en) 2002-12-12 application

Similar Documents

Publication Publication Date Title
Lexer et al. Wavelength-tuning interferometry of intraocular distances
Haberland et al. Chirp optical coherence tomography of layered scattering media
US7400410B2 (en) Optical coherence tomography for eye-length measurement
Drexler et al. Submicrometer precision biometry of the anterior segment of the human eye.
US6057920A (en) Optical coherence tomography with dynamic coherent focus
Yasuno et al. Three-dimensional and high-speed swept-source optical coherence tomography for in vivo investigation of human anterior eye segments
US4938584A (en) Ophthalmic diagnostic method and apparatus
US4993826A (en) Topography measuring apparatus
Hitzenberger Optical measurement of the axial eye length by laser Doppler interferometry.
US5286964A (en) System for detecting, correcting and measuring depth movement of a target
Hitzenberger et al. Three-dimensional imaging of the human retina by high-speed optical coherence tomography
US6779891B1 (en) System and method for non-contacting measurement of the eye
Hitzenberger Measurement of corneal thickness by low-coherence interferometry
US20070291277A1 (en) Spectral domain optical coherence tomography system
US5106183A (en) Topography measuring apparatus
US7072047B2 (en) Method and system for quantitative image correction for optical coherence tomography
Baumgartner et al. Resolution-improved dual-beam and standard optical coherence tomography: a comparison
US6307634B2 (en) Method and apparatus for recording three-dimensional distribution of light backscattering potential in transparent and semi-transparent structures
US7309126B2 (en) Eye characteristics measuring device
US20090168017A1 (en) Refractive prescription using optical coherence tomography
Huang et al. Micron‐resolution ranging of cornea anterior chamber by optical reflectometry
US6658282B1 (en) Image registration system and method
US5521657A (en) Method and system for topographic measurement by measuring the distance between a rigid reference member and a surface of an eye
US6736508B2 (en) Tracking assisted optical procedure
Fercher et al. Slit lamp laser Doppler interferometer

Legal Events

Date Code Title Description
AS Assignment

Owner name: CARL ZEISS JENA GMBH, GERMANY

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:FERCHER, ADOLF FRIEDRICH;BARTH, ROLAND;REEL/FRAME:013294/0247;SIGNING DATES FROM 20020611 TO 20020621

FPAY Fee payment

Year of fee payment: 4

FPAY Fee payment

Year of fee payment: 8

REMI Maintenance fee reminder mailed
LAPS Lapse for failure to pay maintenance fees
FP Expired due to failure to pay maintenance fee

Effective date: 20160907